|Publication number||US4515162 A|
|Application number||US 06/301,861|
|Publication date||May 7, 1985|
|Filing date||Sep 14, 1981|
|Priority date||Mar 14, 1980|
|Publication number||06301861, 301861, US 4515162 A, US 4515162A, US-A-4515162, US4515162 A, US4515162A|
|Inventors||Katsuhiro Yamamoto, Katsuo Matsumoto, Yoshiyuki Okada|
|Original Assignee||Nitto Electric Industrial Co., Ltd.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (7), Referenced by (131), Classifications (11), Legal Events (6)|
|External Links: USPTO, USPTO Assignment, Espacenet|
The present invention relates to an electrode pad, and more particularly, to an electrode pad through which electrical signals from the living body can be transmitted to an electric recording apparatus, such as an electrocardiograph or an electroencephalograph.
The contact between only an electrode terminal plate and the living body does not provide a sufficient electroconductivity, and, therefore, accurate electric signals from the living body cannot be obtained. To overcome this disadvantage, a pasty electrically conductive cream has been used between the electrode terminal plate and the living body. Use of the cream is effective for reducing the noise, but there is a problem in that handling of the cream, and particularly the removal of residual cream from the living body or the electrode after use is troublesome.
Recently, an electrode has been proposed, wherein an electrode terminal plate is combined with an electrically conductive gel pad comprising a cross-linked hydrogel of polyvinyl alcohol permeating a porous carrier. However, since the hydrogel has low cohesive force (requiring the carrier to be used as a gel support), the hydrogel remains on and adheres to the living body to some extent after use.
Investigations have been made to obtain an electrode pad which closely adheres to a living body (e.g., human skin) without formation of a space between the living body and the electrode pad, which results in obtaining a stable record from the start of an electric current flow, and which can be easily handled, and have led the present invention.
One object of the present invention is to provide an electrode pad comprising a tacky cross-linked hydrogel pad adhered to the electrode terminal plate.
Another object of the present invention is to provide an electrode pad comprising a tacky cross-linked hydrogel pad including at least one layer of woven fabric or nonwoven fabric in the electrode pad.
Still another object of the present invention is to provide an electrode pad comprising a tacky cross-linked hydrogel pad including at least one layer composed of woven fabric or nonwoven fabric in the electrode pad and also having a film frame on the side of the electrode pad intended for contacting skin of a living body.
FIG. 1 is a cross-sectional view of the electrode of one use embodiment according to the invention;
FIGS. 2 and 3 are cross-sectional views of the electrode of modified embodiments according to the invention;
FIG. 4 is a cross-sectional view of the electrode of another use embodiment according to the invention;
FIG. 5 is a perspective view of an electrode of a further embodiment according to the invention; and
FIG. 6 is a cross-sectional view of the electrode of still another use embodiment according to the invention.
Throughout the specification, the term "electrode" means a combination of an electrode terminal plate and an electrode pad. That is, an electrode pad is formed on an electrode terminal plate to construct an electrode.
The hydrogel according to the present invention is generally prepared from a hydrophilic polymer, water, and a cross-linking component. Preferably, the hydrogel according to the present invention is composed of (1) at least one of polyacrylic acid and a polyacrylic acid salt, (2) water, and (3) a compound containing at least 2 epoxy groups in the molecule (as a cross-linking component).
The polyacrylic acid and polyacrylic acid salt which can be used in the present invention have an average degree of polymerization of from about 100 to 100,000. Specific examples of polyacrylic acid salt include sodium polyacrylate, triethanolamine polyacrylate, ammonium polyacrylate or potassium polyacrylate. The amount of the polyacrylic acid and/or polyacrylic acid salt used is from about 1 to 80% by weight based on the weight of the hydrogel.
Specific examples of the compound containing at least 2 epoxy groups in the molecule which can be used in the present invention include triglycidyl isocyanurate, polyethylene glycol diglycidyl ether, ethylene glycol diglycidyl ether, glycerine diglycidyl ether, glycerine triglycidyl ether, and the like. The amount of the compound used is from about 0.05 to 5% by weight based on the weight of the hydrogel.
Tackiness of the hydrogel can be controlled by the amount of the cross-linking component. It the amount of the cross-linking component is increased, the strength of the hydrogel increases, but the tackiness tends to decrease.
The hydrogel according to the present invention may contain further additives, such as a polyhydric alcohol as a tackifier (e.g., glycerine, propylene glycol or polyethylene glycol), an electrolyte material (e.g., sodium chloride or potassium chloride), a pH controlling agent, a flexibility imparting agent, an antifungal agent, and the like. The total amount of the additives is from about 3 to 30% by weight based on the weight of the hydrogel.
Water can be present in the hydrogel in an amount of from about 5 to 95% by weight based on the weight of the hydrogel. Water has a function to impart to the hydrogel an electroconductivity necessary to transmit electrical signals, but the electroconductivity is further increased by addition of the electrolyte material. Water also has a function to impart the tackiness.
The hydrogel according to the present invention has an excellent tackiness, for adhering to a living body, and also good electroconductivity, and therefore, a particularly suitable electrode pad is obtained according to the invention.
The electrode pad according to the present invention has a structure such that the tacky cross-linked hydrogel pad is formed on the electrode terminal plate so as to contact the living body, and, therefore, a space is not formed between the electrode pad and the body. Further, the electrode pad has the advantage of an excellent electroconductivity due to a synergistic effect of water and the electrolyte material. Moreover, the electrode pad has further advantage that the cross-linking density is high, so that the hydrogel is not retained on the body after use.
The shape of the hydrogel pad is not particularly limited, but a disk shape or a square plate shape is generally employed.
The size of the hydrogel pad is not also particularly limited and varies according to the intended use. However, from a practical viewpoint, a size of from about 0.5 to 4 cm (side length for a square plate, or a diameter for a disk plate) is preferred.
The thickness of the hydrogel pad is generally from about 0.5 to 10 mm (millimeters). If the thickness is less than about 0.5 mm, contact to the body is poor, and on the other hand, if the thickness is larger than about 10 mm, it is impossible to stably fix the electrode to the living body.
Representative example of the electrode pad according to one use embodiment of the present invention is shown in FIG. 1, wherein 1 is an electrical lead line, 2 is a metal electrode terminal plate, 3 is a tacky cross-linked hydrogel pad equivalent to an electrode pad 5, and 6 is a living body.
Modified examples of the electrode pad according to the present invention are shown in FIGS. 2 and 3, wherein 1, 2 and 3 (=5) are the same as described above, 7 in FIG. 2 is a suction rubber for adhering an electrode to a living body (in this case, the electrode pad is a hollow type), and 8 in FIG. 3 is a support (e.g., a rubber) to fix the electrode terminal plate and the electrode pad.
To improve peelability of the hydrogel pad from the body after use, at least one layer composed of woven fabric or net-like nonwoven fabric is placed in the hydrogel pad.
The arrangement of the woven fabric or net-like nonwoven fabric supports the hydrogel pad, which results in easy handling, prevents self-adhesion of hydrogels which forms a spherical shape during handling, and prevents elongation of the hydrogel pad when peeling it off from the skin. Therefore, it is desired for the fabric to have a repulsion force in a certain degree.
The mesh size of the woven fabric or net-like nonwoven fabric is from about 0.1 to 5.0 mm. If the mesh size is less than about 0.1 mm, the hydrogel does not sufficiently permeate into the fabric, and, as a result, the electric current flow passage is disturbed and, consequently, electrical noise causes during measurement. On the other hand, if the mesh size is larger than about 5.0 mm, the self-supporting property of the fabric is poor.
The thickness of the woven fabric or net-like nonwoven fabric is not particularly limited, but from a practical viewpoint, it generally from about 50 to 400μ.
The material of the woven fabric and net-like nonwoven fabric is not particularly limited, and any conventional natural and synthetic fibers can be used. Representative examples thereof are polyesters, rayon, and the like.
Preferably, two layers of the woven fabric or net-like nonwoven fabric are arranged near the surfaces of the hydrogel pad.
A representative example according to another use embodiment of the present invention is shown in FIG. 4. According to FIG. 4, a disk-like electrode pad 5 having a thickness of 2 mm prepared by placing a polyester woven fabric 4 having a mesh size of 1 mm near the surfaces of the hydrogel pad 3 is adhered on a metal disk (electrode terminal plate) 2 having a diameter of 20 mm which has an electrical lead line 1, and the electrode pad is adhered to the skin 6 such that the pad contacts the skin.
To further improve the peelability of the hydrogel pad from the skin, more particularly, to achieve that where the electrode is peeled off from the living body by pulling the electrode terminal plate after use, the electrode pad is easily separated from the skin but is still sufficiently adhered on the electrode terminal plate, in further use embodiment (FIG. 5) a frame of film is placed on the hydrogel pad so as to contact the skin (i.e., the side contacting the skin).
Material for the film frame is not particularly limited, if the side contacting the skin is non-tacky. Papers, nonwoven fabrics, plastics or the like can be used. Plastics are preferred.
The thickness of the frame is generally from about 10 to 300μ
The width of the frame varies depending upon various factors such as a size of the pad, but from the practical viewpoints, is from about 2 to 8 mm, and preferably from 2 to 5 mm.
In FIGS. 5, 2, 4 and 5 are the same as defined above, and 9 is a frame of film.
As a method for improving the workability of the electrode pad during use, other than the arrangement of the frame film as above there is the method that the hydrogel pad has the two-layered structure, wherein a layer contacting the electrode terminal plate is a strongly tacky layer and a layer contacting the living body is a weakly tacky or non-tacky layer (FIG. 6).
In FIG. 6, 1 to 6 are the same as described above, and 3' is a weakly tacky or non-tacky hydrogel layer. The weakly tacky or non-tacky layer can be easily prepared by controlling the amount of the cross-linking component in the composition of the hydrogel.
The ratio in thickness of the strongly tacky layer 3 and the weakly tacky or non-tacky layer 3' is optional.
The electrode pad according to the present invention contains moisture or salt, and it might be possible to corrode the electrode terminal plate due to the material thereof. It is, therefore, preferred that the electrode terminal plate and the electrode pad are kept separate until use.
In the embodiments shown in FIGS. 1 to 5, the electrode can be fixed on the living body due to tackiness of the electrode pad.
In the embodiment shown in FIG. 6, where the living body moves, the electrode terminal plate is heavy and also the electrode is fixed vertically on the living body, the electrode must be fixed using a fixing band, an adhesive tape, a clip or the like.
While the invention has been described in detail and with reference to specific embodiments thereof, it will be apparent to one skilled in the art that various changes and modifications can be made therein without departing from the spirit and scope thereof.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3998215 *||Apr 23, 1971||Dec 21, 1976||Minnesota Mining And Manufacturing Company||Bio-medical electrode conductive gel pads|
|US4237886 *||Mar 31, 1978||Dec 9, 1980||Sony Corporation||Electrode to be used in contact with a living body|
|US4273135 *||Sep 8, 1978||Jun 16, 1981||Minnesota Mining And Manufacturing Company||Biomedical electrode|
|US4299231 *||Nov 13, 1979||Nov 10, 1981||Beiersdorf Aktiengesellschaft||Electrically conductive, visco-elastic gel and its use in electrode|
|US4391278 *||Feb 14, 1980||Jul 5, 1983||Medtronic, Inc.||Tape electrode|
|WO1981000785A1 *||Aug 4, 1980||Mar 19, 1981||Minnesota Mining & Mfg||Cohesive nonsticky electrically conductive gel composition|
|WO1981002097A1 *||Nov 17, 1980||Aug 6, 1981||Minnesota Mining & Mfg||Conductive adhesive and biomedical electrode|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US4637399 *||Jun 10, 1985||Jan 20, 1987||Fukuda Denshi Co., Ltd.||Waterproof electrode for recording electrocardiogram|
|US4669479 *||Aug 21, 1985||Jun 2, 1987||Spring Creek Institute, Inc.||Dry electrode system for detection of biopotentials|
|US4681118 *||Jun 10, 1985||Jul 21, 1987||Fukuda Denshi Co., Ltd.||Waterproof electrode assembly with transmitter for recording electrocardiogram|
|US4702732 *||Nov 21, 1986||Oct 27, 1987||Trustees Of Boston University||Electrodes, electrode assemblies, methods, and systems for tissue stimulation and transdermal delivery of pharmacologically active ligands|
|US4786277 *||Jul 24, 1987||Nov 22, 1988||Trustees Of Boston University||Electrodes, electrode assemblies, methods, and systems for tissue stimulation|
|US4791933 *||Feb 19, 1987||Dec 20, 1988||Fukuda Denshi Co., Ltd.||Radio electrocardiography for a living body moving in the water|
|US4989607 *||Mar 30, 1989||Feb 5, 1991||Preston Keusch||Highly conductive non-stringy adhesive hydrophilic gels and medical electrode assemblies manufactured therefrom|
|US5124076 *||Jan 19, 1990||Jun 23, 1992||Contour Electrodes, Inc.||Rapid, curing, electrically conductive adhesive|
|US5143071 *||Mar 26, 1990||Sep 1, 1992||Nepera, Inc.||Non-stringy adhesive hydrophilic gels|
|US5183599 *||Jun 18, 1991||Feb 2, 1993||Smuckler Jack H||Rapid curing, electrically conductive adhesive|
|US5261402 *||Jul 20, 1992||Nov 16, 1993||Graphic Controls Corporation||Snapless, tabless, disposable medical electrode with low profile|
|US5311658 *||Aug 21, 1992||May 17, 1994||Fukuda Denshi Co., Ltd.||Apparatus for producing living body leading electrode|
|US5331959 *||Aug 16, 1991||Jul 26, 1994||Physiometrix, Inc.||Low impedance, low durometer, dry conforming contact member|
|US5348008 *||Mar 19, 1992||Sep 20, 1994||Somnus Corporation||Cardiorespiratory alert system|
|US5353793 *||Nov 25, 1991||Oct 11, 1994||Oishi-Kogyo Company||Sensor apparatus|
|US5354790 *||Aug 31, 1992||Oct 11, 1994||Nepera, Inc.||Methods for the preparation of non-stringy adhesive hydrophilic gels|
|US5372125 *||Aug 13, 1993||Dec 13, 1994||Ludlow Corporation||Positive locking biomedical electrode and connector system|
|US5474065 *||Apr 4, 1994||Dec 12, 1995||Graphic Controls Corporation||Non-invasive fetal probe|
|US5511548 *||Nov 7, 1994||Apr 30, 1996||New Dimensions In Medicine, Inc.||Biomedical electrode having a secured one-piece conductive terminal|
|US5522878 *||Apr 26, 1993||Jun 4, 1996||Lectec Corporation||Solid multipurpose ultrasonic biomedical couplant gel in sheet form and method|
|US5536263 *||Mar 30, 1994||Jul 16, 1996||Lectec Corporation||Non-occulusive adhesive patch for applying medication to the skin|
|US5540033 *||Jan 10, 1994||Jul 30, 1996||Cambrex Hydrogels||Integrated Manufacturing process for hydrogels|
|US5596038 *||May 16, 1994||Jan 21, 1997||Physiometrix, Inc.||Hydrogel having a silicon-based crosslinker for biosensors and electrodes|
|US5617871 *||Dec 1, 1994||Apr 8, 1997||Quinton Instrument Company||Spread spectrum telemetry of physiological signals|
|US5665477 *||Jun 7, 1995||Sep 9, 1997||Graphic Controls Corporation||Hydrogel adhesive for attaching medical device to patient|
|US5700478 *||Aug 19, 1994||Dec 23, 1997||Cygnus, Inc.||Water-soluble pressure-sensitive mucoadhesive and devices provided therewith for emplacement in a mucosa-lined body cavity|
|US5727550 *||Apr 9, 1996||Mar 17, 1998||Lectec Corporation||Dual purpose ultrasonic biomedical couplant pad and electrode|
|US5741510 *||Apr 8, 1996||Apr 21, 1998||Lectec Corporation||Adhesive patch for applying analgesic medication to the skin|
|US5817016 *||Aug 28, 1996||Oct 6, 1998||Physiometrix, Inc.||Electrical conductor using hydrogel and method|
|US5833622 *||Oct 31, 1996||Nov 10, 1998||Graphic Controls Corporation||Non-invasive fetal probe having improved mechanical and electrical properties|
|US6038464 *||Feb 9, 1998||Mar 14, 2000||Axelgaard Manufacturing Co., Ltd.||Medical electrode|
|US6096333 *||Oct 8, 1997||Aug 1, 2000||Lectec Corporation||Method of forming adhesive patch for applying medication to the skin|
|US6096334 *||Dec 14, 1998||Aug 1, 2000||Lectec Corporation||Adhesive patch for applying medication to the skin and method|
|US6169915 *||Jan 13, 1997||Jan 2, 2001||Ufz-Umweltforschungszentrum Leipzighalle Gmbh||Device for fastening of sensors to the surface of the skin and a method for detecting the removal of sensors from the surface of the skin|
|US6198955 *||Sep 29, 1999||Mar 6, 2001||Axelgaard Manufacturing Co., Ltd||Medical electrode method of manufacture|
|US6263226 *||Nov 2, 1999||Jul 17, 2001||Axelgaard Manufacturing Co., Ltd.||Sponge electrode|
|US6418333 *||Oct 2, 2000||Jul 9, 2002||Axelgaard Manufacturing Co., Ltd.||Floating electrode|
|US6469227||May 12, 2000||Oct 22, 2002||Lectec Corporation||Antipruritic patch|
|US6643532 *||Jun 14, 2002||Nov 4, 2003||Axelgaard Manufacturing Co. Ltd.||Floating electrode|
|US6800278||Feb 14, 2000||Oct 5, 2004||Ballard Medical Products, Inc.||Inherently antimicrobial quaternary amine hydrogel wound dressings|
|US6845272||May 25, 1999||Jan 18, 2005||Medicotest A/S||Skin electrode|
|US6856840 *||Aug 3, 2001||Feb 15, 2005||Intermedics, Inc.||Ionically conductive polymeric composition|
|US7146228||Jul 11, 2001||Dec 5, 2006||Medicotest A/S||Skin electrode with a by-pass element|
|US7357891||Jan 30, 2004||Apr 15, 2008||Monosol Rx, Llc||Process for making an ingestible film|
|US7425292||Feb 14, 2002||Sep 16, 2008||Monosol Rx, Llc||Thin film with non-self-aggregating uniform heterogeneity and drug delivery systems made therefrom|
|US7666337||May 28, 2004||Feb 23, 2010||Monosol Rx, Llc||Polyethylene oxide-based films and drug delivery systems made therefrom|
|US7729781 *||Mar 14, 2007||Jun 1, 2010||Greatbatch Ltd.||High efficiency neurostimulation lead|
|US7824588||Apr 14, 2008||Nov 2, 2010||Monosol Rx, Llc||Method of making self-supporting therapeutic active-containing film|
|US7910641||Dec 14, 2006||Mar 22, 2011||Monosol Rx, Llc||PH modulated films for delivery of actives|
|US7972618||Sep 20, 2007||Jul 5, 2011||Monosol Rx, Llc||Edible water-soluble film containing a foam reducing flavoring agent|
|US8017150||Apr 22, 2008||Sep 13, 2011||Monosol Rx, Llc||Polyethylene oxide-based films and drug delivery systems made therefrom|
|US8121664 *||Aug 20, 2008||Feb 21, 2012||Dayton Technologies Limited||Sensor|
|US8475832||Aug 7, 2009||Jul 2, 2013||Rb Pharmaceuticals Limited||Sublingual and buccal film compositions|
|US8603514||Jul 10, 2007||Dec 10, 2013||Monosol Rx, Llc||Uniform films for rapid dissolve dosage form incorporating taste-masking compositions|
|US8652378||Mar 29, 2013||Feb 18, 2014||Monosol Rx Llc||Uniform films for rapid dissolve dosage form incorporating taste-masking compositions|
|US8663687||May 13, 2010||Mar 4, 2014||Monosol Rx, Llc||Film compositions for delivery of actives|
|US8685437||Mar 26, 2009||Apr 1, 2014||Monosol Rx, Llc||Thin film with non-self-aggregating uniform heterogeneity and drug delivery systems made therefrom|
|US8706183||Jun 30, 2008||Apr 22, 2014||University Of Pittsburgh-Of The Commonwealth System Of Higher Education||Electrode systems, devices and methods|
|US8765167||Sep 8, 2006||Jul 1, 2014||Monosol Rx, Llc||Uniform films for rapid-dissolve dosage form incorporating anti-tacking compositions|
|US8900497||Aug 23, 2013||Dec 2, 2014||Monosol Rx, Llc||Process for making a film having a substantially uniform distribution of components|
|US8900498||Aug 23, 2013||Dec 2, 2014||Monosol Rx, Llc||Process for manufacturing a resulting multi-layer pharmaceutical film|
|US8906277||Aug 23, 2013||Dec 9, 2014||Monosol Rx, Llc||Process for manufacturing a resulting pharmaceutical film|
|US8974826||Jun 10, 2011||Mar 10, 2015||Monosol Rx, Llc||Nanoparticle film delivery systems|
|US9108340||Aug 23, 2013||Aug 18, 2015||Monosol Rx, Llc||Process for manufacturing a resulting multi-layer pharmaceutical film|
|US9126055||Apr 20, 2012||Sep 8, 2015||Cardiac Science Corporation||AED faster time to shock method and device|
|US9506029||Dec 30, 2011||Nov 29, 2016||University Of Massachusetts Lowell||Responsive cell culture hydrogel|
|US9554976||Jul 30, 2013||Jan 31, 2017||The Procter & Gamble Company||Tooth whitening product|
|US9687454||Jan 6, 2016||Jun 27, 2017||Indivior Uk Limited||Sublingual and buccal film compositions|
|US20020120332 *||Dec 3, 2001||Aug 29, 2002||Law Tom J.||Method and apparatus for securing external device to patient|
|US20030107149 *||Feb 14, 2002||Jun 12, 2003||International Fluidics.||Thin film with non-self-aggregating uniform heterogeneity and drug delivery systems made therefrom|
|US20030130714 *||May 28, 2001||Jul 10, 2003||Brian Nielsen||Electrode for establishing electrical contact with the skin|
|US20030178298 *||Jul 25, 2001||Sep 25, 2003||Thomas Bassoe||Electromedical electrode with a snap connecting means|
|US20040015222 *||Jul 11, 2001||Jan 22, 2004||Brian Nielsen||Skin electrode with a by-pass element|
|US20040159541 *||Feb 17, 2004||Aug 19, 2004||Wei-Kung Wang||Apparatus for selectively moving hydrogen ions in aqueous solutions|
|US20040230167 *||Apr 22, 2004||Nov 18, 2004||Steiner Ventures Llc||Pad for cleaning and hydrating skin|
|US20040258896 *||Jan 30, 2004||Dec 23, 2004||Monosolrx Llc.||Thin film with non-self-aggregating uniform heterogeneity and drug delivery systems made therefrom|
|US20050037055 *||May 28, 2004||Feb 17, 2005||Monosolrx Llc.||Polyethylene oxide-based films and drug delivery systems made therefrom|
|US20050184427 *||Mar 29, 2005||Aug 25, 2005||Monosolrx, Llc.||Thin film with non-self-aggregating uniform heterogeneity and drug delivery systems made therefrom|
|US20050238591 *||Jun 21, 2005||Oct 27, 2005||Sagel Paul A||Tooth whitening substances|
|US20060039958 *||Sep 28, 2005||Feb 23, 2006||Monosolrx, Llc.||Multi-layer films having uniform content|
|US20060147493 *||Jul 22, 2003||Jul 6, 2006||Yang Robert K||Packaging and dispensing of rapid dissolve dosage form|
|US20070069416 *||Jun 22, 2006||Mar 29, 2007||Monosolrx, Llc||Thin film with non-self-aggregating uniform heterogeneity and drug delivery systems made therefrom|
|US20070122455 *||Sep 8, 2006||May 31, 2007||Monosolrx, Llc.||Uniform films for rapid-dissolve dosage form incorporating anti-tacking compositions|
|US20070149731 *||Dec 14, 2006||Jun 28, 2007||Monosolrx, Llc.||PH modulated films for delivery of actives|
|US20070154527 *||Dec 5, 2006||Jul 5, 2007||Monosoirx, Llc||Topical film compositions for delivery of actives|
|US20070172515 *||Jan 19, 2007||Jul 26, 2007||Monosolrx, Llc||Film bandage for mucosal administration of actives|
|US20070190157 *||Jan 19, 2007||Aug 16, 2007||Monosoirx, Llc.||Film lined packaging and method of making same|
|US20070219608 *||Mar 14, 2007||Sep 20, 2007||Swoyer John M||High efficiency neurostimulation lead|
|US20070235716 *||Mar 21, 2007||Oct 11, 2007||Emir Delic||Electrode|
|US20070238945 *||Mar 21, 2007||Oct 11, 2007||Emir Delic||Electrode Headset|
|US20070281003 *||Feb 13, 2007||Dec 6, 2007||Fuisz Richard C||Polymer-Based Films and Drug Delivery Systems Made Therefrom|
|US20080025927 *||Jul 31, 2007||Jan 31, 2008||Sagel Paul A||Delivery system for an oral care substance|
|US20080044454 *||Jul 10, 2007||Feb 21, 2008||Monosolrx Llc||Uniform films for rapid dissolve dosage form incorporating taste-masking compositions|
|US20080075825 *||Sep 20, 2007||Mar 27, 2008||Fuisz Richard C||Edible Water-Soluble Film Containing a Foam Reducing Flavoring Agent|
|US20080081071 *||Sep 28, 2007||Apr 3, 2008||Pradeep Sanghvi||Film Embedded Packaging and Method of Making Same|
|US20080260805 *||Apr 14, 2008||Oct 23, 2008||Monosol Rx, Llc||Thin film with non-self-aggregating uniform heterogeneity and drug delivery systems made therefrom|
|US20080260809 *||Apr 22, 2008||Oct 23, 2008||Monosol Rx, Llc||Polyethylene oxide-based films and drug delivery systems made therefrom|
|US20090005667 *||Jun 30, 2008||Jan 1, 2009||Xinyan Cui||Electrode systems, devices and methods|
|US20090105576 *||Oct 22, 2007||Apr 23, 2009||Nam Hoai Do||Electrode conductive element|
|US20090181069 *||Mar 26, 2009||Jul 16, 2009||Monosol Rx, Llc||Thin film with non-self-aggregating uniform heterogeneity and drug delivery systems made therefrom|
|US20100004524 *||Aug 20, 2008||Jan 7, 2010||Dayton Technologies Limited||Sensor|
|US20100021526 *||Oct 7, 2009||Jan 28, 2010||Monosol Rx, Llc||Ph modulated films for delivery of actives|
|US20100072060 *||Sep 25, 2008||Mar 25, 2010||Tyco Healthcare Group Lp||Biomedical Electrode and Method of Formation Thereof|
|US20100075532 *||Sep 25, 2008||Mar 25, 2010||Tyco Healthcare Group Lp||Fluorescent Marker for Detecting Gel or Lack of Gel|
|US20100076294 *||Sep 25, 2008||Mar 25, 2010||Tyco Healthcare Group Lp||System and Method of Prepping Skin Prior to Electrode Application|
|US20110033541 *||Aug 7, 2009||Feb 10, 2011||Monosol Rx, Llc||Sublingual and buccal film compositions|
|US20110033542 *||Aug 7, 2009||Feb 10, 2011||Monosol Rx, Llc||Sublingual and buccal film compositions|
|USRE42126||Jun 30, 2000||Feb 8, 2011||The Procter & Gamble Company||Delivery system for oral care compositions comprising organosiloxane resins using a removable backing strip|
|EP0217383A2 *||Oct 1, 1986||Apr 8, 1987||Fukuda Denshi Co., Ltd.||Electrocadiographic electrode|
|EP0217383A3 *||Oct 1, 1986||Aug 17, 1988||Fukuda Denshi Co., Ltd.||Electrocadiographic electrode|
|EP0217384A2 *||Oct 1, 1986||Apr 8, 1987||Fukuda Denshi Co., Ltd.||Electrocadiographic electrode|
|EP0217384A3 *||Oct 1, 1986||Aug 17, 1988||Fukuda Denshi Co., Ltd.||Electrocadiographic electrode|
|EP0251774A2 *||Jun 30, 1987||Jan 7, 1988||Nepera, Inc.||Solid sheet of an adhesive hydrophilic gel and method for its production|
|EP0251774A3 *||Jun 30, 1987||Sep 6, 1989||Nepera, Inc.||Solid sheet of an adhesive hydrophilic gel and method for its production|
|EP0676170A1 *||Apr 4, 1995||Oct 11, 1995||Graphic Controls Corporation||Non-invasive fetal probe|
|EP1052933A2 *||Feb 4, 1999||Nov 22, 2000||Axelgaard Manufacturing Company Ltd||Medical electrode and method of manufacture|
|EP1052933A4 *||Feb 4, 1999||Dec 3, 2008||Axelgaard Mfg Co Ltd||Medical electrode and method of manufacture|
|EP1195137A1 *||Sep 25, 1999||Apr 10, 2002||Medicotest A/S||A skin electrode|
|WO1988003821A1 *||Nov 6, 1987||Jun 2, 1988||Boston University||Electrode assembly for transdermal drug delivery|
|WO1993010706A1 *||Oct 28, 1992||Jun 10, 1993||Oishi Kogyo Company||Sensor apparatus|
|WO1999039635A1 *||Feb 4, 1999||Aug 12, 1999||Axelgaard Manufacturing Company, Ltd.||Medical electrode and method of manufacture|
|WO2000071024A1 *||May 25, 1999||Nov 30, 2000||Medicotest A/S||A skin electrode|
|WO2002028279A1 *||Oct 1, 2001||Apr 11, 2002||Axelgaard Manufacturing, Ltd.||Floating electrode|
|WO2004093833A2 *||Apr 22, 2004||Nov 4, 2004||Biodel, Inc.||Pad for cleaning and hydrating skin|
|WO2004093833A3 *||Apr 22, 2004||Dec 23, 2004||Solomon S Steiner||Pad for cleaning and hydrating skin|
|WO2009006397A2 *||Jun 30, 2008||Jan 8, 2009||University Of Pittsburgh-Of The Commonwealth System Of Higher Education||Electrode systems and methods comprising a hydrophilic swollen polymer|
|WO2009006397A3 *||Jun 30, 2008||Mar 5, 2009||Univ Pittsburgh||Electrode systems and methods comprising a hydrophilic swollen polymer|
|WO2009055455A2 *||Oct 22, 2008||Apr 30, 2009||Emotiv Systems Pty Ltd||Electrode conductive element|
|WO2009055455A3 *||Oct 22, 2008||Jul 2, 2009||Emotiv Systems Pty Ltd||Electrode conductive element|
|WO2012092542A2 *||Dec 30, 2011||Jul 5, 2012||University Of Massachusetts Lowell||Responsive cell culture hydrogel|
|WO2012092542A3 *||Dec 30, 2011||Apr 10, 2014||University Of Massachusetts Lowell||Responsive cell culture hydrogel|
|U.S. Classification||600/391, 252/500, 600/397|
|International Classification||A61B5/0408, C08L63/00, C09J133/02|
|Cooperative Classification||C08L63/00, C09J133/02, A61B5/04087|
|European Classification||C09J133/02, A61B5/0408F|
|Feb 27, 1985||AS||Assignment|
Owner name: NITTO ELECTRIC INDUSRIAL CO., LTD., NO. 1-2, SHIMO
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST.;ASSIGNORS:YAMAMOTO, KATSUHIRO;MATSUMOTO, KATSUO;OKADA, YOSHIYUKI;REEL/FRAME:004365/0978
Effective date: 19810901
|Oct 7, 1988||FPAY||Fee payment|
Year of fee payment: 4
|Oct 23, 1992||FPAY||Fee payment|
Year of fee payment: 8
|Dec 10, 1996||REMI||Maintenance fee reminder mailed|
|May 4, 1997||LAPS||Lapse for failure to pay maintenance fees|
|Jul 15, 1997||FP||Expired due to failure to pay maintenance fee|
Effective date: 19970507